EP0302186A2 - Medical device and method for making it - Google Patents
Medical device and method for making it Download PDFInfo
- Publication number
- EP0302186A2 EP0302186A2 EP88107039A EP88107039A EP0302186A2 EP 0302186 A2 EP0302186 A2 EP 0302186A2 EP 88107039 A EP88107039 A EP 88107039A EP 88107039 A EP88107039 A EP 88107039A EP 0302186 A2 EP0302186 A2 EP 0302186A2
- Authority
- EP
- European Patent Office
- Prior art keywords
- medical device
- isocyanate
- polyol
- metal ion
- chain extenders
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Granted
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L27/00—Materials for grafts or prostheses or for coating grafts or prostheses
- A61L27/50—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
- A61L27/54—Biologically active materials, e.g. therapeutic substances
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L29/00—Materials for catheters, medical tubing, cannulae, or endoscopes or for coating catheters
- A61L29/14—Materials characterised by their function or physical properties, e.g. lubricating compositions
- A61L29/16—Biologically active materials, e.g. therapeutic substances
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/10—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing inorganic materials
- A61L2300/102—Metals or metal compounds, e.g. salts such as bicarbonates, carbonates, oxides, zeolites, silicates
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/10—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices containing or releasing inorganic materials
- A61L2300/102—Metals or metal compounds, e.g. salts such as bicarbonates, carbonates, oxides, zeolites, silicates
- A61L2300/104—Silver, e.g. silver sulfadiazine
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
- A61L2300/00—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices
- A61L2300/40—Biologically active materials used in bandages, wound dressings, absorbent pads or medical devices characterised by a specific therapeutic activity or mode of action
- A61L2300/404—Biocides, antimicrobial agents, antiseptic agents
Definitions
- the present invention relates to a medical device according to the preamble of claim 1 and a method for its production.
- microbicidal effect of heavy metal ions such as gold, silver or copper, which is often referred to as oligodynamic in the literature (e.g.: The Journal of Urology, 121 ⁇ January 1979>, 40 ff.), Is used in medical technology for plastic endoprostheses or tubular catheters , such as B. urethral catheter for a long period of time to equip microbicidal.
- the US-PS 4,054,139 proposes to this end, a tubular catheter on its inner and outer surface with at least one oligodynamic agent, e.g. B. silver or its compounds.
- at least one oligodynamic agent e.g. B. silver or its compounds.
- the alternative of manufacturing the matrix for the metal ion-donating substances from polyurethane allows the reversible embedding of these substances down to the innermost material zones, since polyurethane is also sufficiently hydrophilic inside and could therefore release metal ions under the influence of body fluid.
- devices constructed in this way as measurements have shown, have such low delivery rates for oligodynamically active substances that a sufficient amount of effective ions, measured in terms of the concentration of the germs to be destroyed, is not available for continuous use.
- thermoplastic polyurethane-silicone elastomer material From EP-PS 0 068 385 the pronounced antithrombogenic effect of a thermoplastic polyurethane-silicone elastomer material and its advantageous use for medical molded parts that are brought into direct contact with blood have become known.
- Block copolymers of a polyurethane and an organic silicone polymer with fewer silicone than polyurethane units which are known from US Pat. No. 3,562,352, are discussed there with regard to their mechanical and antithrombogenic properties in direct blood contact, and a new, advantageous variant is described in detail: These are: 4 to 15% by weight of an organic silicone polymer with a molecular weight of 500 to 10,000 and plasticizing polyether or polyester segments are introduced into the polymer main chain.
- This material also contains no medically effective active ingredients to be released; the European patent specification does not contain any indication of its usability for medical devices which have a microbicidal action and are not associated with blood.
- the invention has for its object to provide a medical device to be used in the living body, tissue penetrating body tissue, which has a significantly increased delivery capacity for microbicidal, metal ion-releasing substances and good tissue tolerance and which the metal ions in a controlled amount over a longer period of time to each of them Is able to give back the outside when it comes into contact with body fluid.
- tissue penetrating body tissue which has a significantly increased delivery capacity for microbicidal, metal ion-releasing substances and good tissue tolerance and which the metal ions in a controlled amount over a longer period of time to each of them Is able to give back the outside when it comes into contact with body fluid.
- a method for producing such a medical device is to be demonstrated, with spatially uniform embedding of the metal ion-releasing substance in finely divided form in the polymer matrix being possible even during its production without complicated mechanical or chemical aftertreatment of the material or the finished part.
- silicon polyurethane The material class known per se proposed according to the invention is hereinafter referred to as "silicone polyurethane".
- the production and properties of this material are not critical to the present invention and, depending on the desired requirements, can be derived from the prior art without inventive step within the framework of the claimed teaching.
- metal salts As a metal ion, microbicidal, oligodynamically active substance z.
- the spatial embedding of the active substances into the silicone-polyurethane matrix according to the invention by 1 to 15 percent increases the usable amount of the ions available compared to the usual coatings by 40% and more.
- the invention is preferably, but not exclusively, to be used when the devices in question must remain in contact with body tissue not only temporarily, but longer; it includes e.g. B. endoprostheses, catheters, probes, endoscopes, implants and drainage.
- the polymer matrix made of silicone polyurethane which forms the device according to the invention contains the entire oligodynamic active ingredient, in addition to the advantage of releasing the metal ions to both outer surfaces of the device body, there is also the advantageous effect that at the beginning of the application, where an increased number of Bacteria, microbes and germs can be present, an increased amount of active ingredient is released as soon as all surface areas of the matrix are saturated with body fluid. After a longer period of time, there is a steadily decreasing supply of metal ions, the release of which is now determined by their path length during the migration from the interior of the matrix to its surface.
- the configuration of the medical device according to the invention thus automatically adjusts the rate of release of metal ions to the amount of organisms to be controlled.
- the metal ion-releasing substance should expediently not contain any grain sizes larger than 50 ⁇ m, since exceeding this limit can have a negative effect on the mechanical stability of the matrix.
- a preferred method for producing the device according to the invention is that the polypol, the organic silicone polymer and the isocyanate and, if appropriate, the chain extenders and / or crosslinking substances are allowed to react with one another and then brought into the desired shape.
- the metal ion-donating substance with a proportion of the total polymer mass of 1 to 15% by weight is admixed as a powder with a grain size ⁇ 50 ⁇ m before the addition of the isocyanate and dewatered together with the polyol.
- a further, particularly preferred method consists in using a readily water-soluble, metal ion-releasing substance instead of the powder and admixing it as an aqueous solution with a solids content as in the powder addition described above and at the same point as above, and then dewatered and then add the isocyanate.
- This variant of the method offers the advantage of being able to introduce the active substance into the matrix in the smallest possible form, namely as discrete ions and thus in an optimally uniform manner.
- a one-step shaping and bactericidal / microbicidal treatment of the medical device is achieved. Any post-treatment is eliminated, which completely eliminates the handling of solvents, the swelling or dissolving of the substrate or problems with the adhesion of coatings.
- thermoplastic material If you want to obtain a thermoplastic material, the finished polyurethane with active ingredient is granulated, dried and then either injection molded or extruded.
- thermoset devices e.g. B. probes, the shaping takes place immediately after the reaction of the starting materials by pouring into a molded part.
- the desired medical device can be manufactured in a continuous process step.
- the following example describes a manufacturing method for a medical device made of a thermoplastic material in a non-restrictive manner:
- the finished product is allowed to harden on the hot plate, then granulated and dried in a warm air oven at 110 ° C. for two hours. Finally, the granules are shaped into an urethral catheter on an injection molding machine.
- the catheter manufactured in this way has the following material properties: Tensile strength (DIN 53 504): 20 MPa Elongation at break (DIN 53 504): 500% Hardness (DIN 53 305): 70 shore A These material data show the mechanical suitability of the thermoplastic material for the production of catheters and implants.
Abstract
Description
Die vorliegende Erfindung betrifft ein medizinisches Gerät nach dem Oberbegriff des Anspruchs 1 sowie ein Verfahren zu seiner Herstellung.The present invention relates to a medical device according to the preamble of claim 1 and a method for its production.
Die in der Literatur (z.B.: The Journal of Urology, 121 <Januar 1979>, 40 ff.) häufig als oligodynamisch bezeichnete Mikrobizidwirkung von schwermetallionen, wie Gold, Silber oder Kupfer, wird in der Medizintechnik genutzt, um Kunststoff-Endoprothesen oder Schlauchförmige Katheter, wie z. B. Harnröhrenkatheter, für eine längere Zeitdauer mikrobizid auszurüsten.The microbicidal effect of heavy metal ions such as gold, silver or copper, which is often referred to as oligodynamic in the literature (e.g.: The Journal of Urology, 121 <January 1979>, 40 ff.), Is used in medical technology for plastic endoprostheses or tubular catheters , such as B. urethral catheter for a long period of time to equip microbicidal.
Die US-PS 4,054,139 schlägt hierzu vor, einen röhrenförmigen Katheter auf seiner Innen- und auf seiner Außenfläche mit mindestens einem oligodynamischen Agens, z. B. Silber oder seinen Verbindungen, zu versehen.The US-PS 4,054,139 proposes to this end, a tubular catheter on its inner and outer surface with at least one oligodynamic agent, e.g. B. silver or its compounds.
Um die Oberfläche eines solchen medizinischen Gerätes in quantitativer Hinsicht noch aufnahmefähiger für Metallionen abgebende Substanzen zu machen, wird in der US-PS 4,612,337 gelehrt, das Polymermaterial, z. B. ein Polyurethan oder Silikon-Elastomer, durch zweimaliges Tränken bzw. Quellen mit geeigneten Lösungsmitteln (für das Mikrobizid bzw. für das Metallsalz) zu behandeln und jeweils anschließend, zuletzt nach dem Auswaschen, zu trocknen.In order to make the surface of such a medical device quantitatively more receptive to metal ion donating substances, it is taught in US Pat. No. 4,612,337 that the polymer material, e.g. B. a polyurethane or silicone elastomer, by twice impregnating or swelling with suitable solvents (for the microbicide or for the metal salt) and then to dry each time, finally after washing.
Unbefriedigend ist bei allen bekannten Lösungen, bei denen eine innen- und außenseitige mikrobizide Ausrüstung des Gerätes erwünscht ist, der hohe Arbeitsaufwand des Beschichtens der Oberflächen.In all known solutions in which an inside and outside microbicidal treatment of the device is desired, the high workload of coating the surfaces is unsatisfactory.
Da ferner die Metallionen abgebenden Substanzen stets nur in den Oberflächenbereichen des Polymerwerkstoffes gebunden vorliegen, ist ihre Verfügbarkeit zeitlich und mengenmäßig begrenzt, was bei Langzeitbehandlungen einen häufigen, risikoreichen und schmerzhaften Austausch mit neu beschichteten Geräten erforderlich macht.Furthermore, since the substances that give off metal ions are always bound only in the surface areas of the polymer material, their availability is limited in terms of time and quantity, which means that long-term treatments require frequent, risky and painful exchanges with newly coated devices.
Für alle nicht flächig aufgebauten, sondern eine Raumformaufweisenden, intracorporal zu verwendenden Geräte, z. B. Katheter oder Prothesen, stößt man bereits bei etwas größeren Materialdicken an die Grenzen der Einlagerungs- oder Abgabefähigkeit für Metallionen abgebende Substanzen: Im Falle von Silikon-Elastomeren scheitert man daran, daß die inneren Bereiche dieses Materials wegen ihrer Hydrophobie für Körperflüssigkeit nicht oder nicht in ausreichendem Maße zugänglich sind. Dies bedeutet jedoch nichts anderes, als daß den tiefer in die Matrix eingebetteten Ionen kein Trägermedium mehr zur Verfügung steht, mittels dessen sie wieder nach außen wandern könnten, um ihre mikrobizide Wirkung in dem den Katheter umgebenden Körpergewebe zu entfalten. Es sind somit nach wie vor lediglich die an der Oberfläche befindlichen Agenzien wirksam.For all devices that are not flat, but have a spatial shape that can be used intracorporeally, e.g. B. catheters or prostheses, one reaches the limits of the storage or dispensing ability for metal ion-releasing substances even with somewhat larger material thicknesses: In the case of silicone elastomers, one fails because the inner areas of this material do not or not because of their hydrophobicity for body fluids are sufficiently accessible. However, this means nothing other than that the carrier medium is no longer available to the ions embedded deeper into the matrix, by means of which they could migrate outward again in order to develop their microbicidal action in the body tissue surrounding the catheter. Only the agents on the surface are still effective.
Die Alternative, die Matrix für die Metallionen abgebenden Substanzen aus Polyurethan zu fertigen, läßt zwar die reversible Einbettung dieser Substanzen bis in innerste Werkstoffzonen zu, da Polyurethan ausreichend hydrophil auch in seinem Innern ist und unter Einwirkung von Körperflüssigkeit somit durchaus Metallionen abgeben könnte. Solchermaßen aufgebaute Geräte jedoch weisen, wie Messungen ergaben, derart niedrige Abgaberaten für oligodynamisch wirksame Substanzen auf, daß eine, gemessen an der Konzentration der zu vernichtenden Keime, ausreichende Menge an wirksamen Ionen bei Daueranwendung nicht zur Verfügung steht.The alternative of manufacturing the matrix for the metal ion-donating substances from polyurethane allows the reversible embedding of these substances down to the innermost material zones, since polyurethane is also sufficiently hydrophilic inside and could therefore release metal ions under the influence of body fluid. However, devices constructed in this way, as measurements have shown, have such low delivery rates for oligodynamically active substances that a sufficient amount of effective ions, measured in terms of the concentration of the germs to be destroyed, is not available for continuous use.
Aus der EP-PS 0 068 385 ist die ausgeprägt antithrombogene Wirkung eines thermoplastischen Polyurethan-Silikon-Elastomerwerkstoffes und dessen vorteilhafte Verwendung für medizinische Formteile, die unmittelbar mit Blut in Kontakt gebracht werden, bekanntgeworden. Es werden dort aus der US-PS 3,562,352 vorbekannte Block-Copolymere aus einem Polyurethan und einem organischen Silikonpolymeren mit weniger Silikon- als Polyurethan-Einheiten bezüglich ihrer mechanischen sowie antithrombogenen Eigenschaften bei unmittelbarem Blutkontakt diskutiert sowie eine neuartige, vorteilhafte Variante ausführlich beschrieben: Bei dieser sind in die Polymer-Hauptkette 4 bis 15 Gew.-% eines organischen Silikonpolymeren mit einem Molekulargewicht von 500 bis 10.000 und weichmachende Polyether- oder Polyester-Segmente eingebracht. Auch dieser Werkstoff enthält keine medizinisch wirksamen, nach außen abzugebenden Wirkstoffe; ein Hinweis auf seine Verwendbarkeit für mikrobizid wirkende, nicht mit Blut in Verbindung stehende medizinische Geräte ist auch in der Europäischen Patentschrift nicht enthalten.From EP-PS 0 068 385 the pronounced antithrombogenic effect of a thermoplastic polyurethane-silicone elastomer material and its advantageous use for medical molded parts that are brought into direct contact with blood have become known. Block copolymers of a polyurethane and an organic silicone polymer with fewer silicone than polyurethane units, which are known from US Pat. No. 3,562,352, are discussed there with regard to their mechanical and antithrombogenic properties in direct blood contact, and a new, advantageous variant is described in detail: These are: 4 to 15% by weight of an organic silicone polymer with a molecular weight of 500 to 10,000 and plasticizing polyether or polyester segments are introduced into the polymer main chain. This material also contains no medically effective active ingredients to be released; the European patent specification does not contain any indication of its usability for medical devices which have a microbicidal action and are not associated with blood.
Der Erfindung liegt die Aufgabe zugrunde, ein im lebenden Körper zu verwendendes, Körpergewebe durchdringendes medizinisches Gerät anzugeben, welches eine wesentlich erhöhte Abgabekapazität für mikrobizide, Metallionen abgebende Substanzen und eine gute Gewebeverträglichkeit aufweist und welches die Metallionen in kontrollierter Menge über einen längeren Zeitraum zu jeder seiner Außenseiten wieder abzugeben imstande ist, wenn es mit Körperflüssigkeit in Berührung kommt. Zugleich soll ein Verfahren zur Herstellung eines solchen medizinischen Gerätes aufgezeigt werden, wobei ohne umständliche mechanische oder chemische Nachbehandlung des Werkstoffes oder des Fertigteils eine räumlich gleichmäßige Einbettung der Metallionen abgebenden Substanz in feinst verteilter Form in die Polymermatrix bereits während deren Herstellung möglich ist.The invention has for its object to provide a medical device to be used in the living body, tissue penetrating body tissue, which has a significantly increased delivery capacity for microbicidal, metal ion-releasing substances and good tissue tolerance and which the metal ions in a controlled amount over a longer period of time to each of them Is able to give back the outside when it comes into contact with body fluid. At the same time, a method for producing such a medical device is to be demonstrated, with spatially uniform embedding of the metal ion-releasing substance in finely divided form in the polymer matrix being possible even during its production without complicated mechanical or chemical aftertreatment of the material or the finished part.
Die Lösung dieser Aufgabe besteht, ausgehend von US-PS 4,054,139, in einen gattungsgemäßen medizinischen Gerät mit den kennzeichnenden Merkmalen des Anspruchs 1. Besonders bevorzugte Herstellungsverfahren werden in den Ansprüchen 2 und 3 dargelegt.This problem is solved, starting from US Pat. No. 4,054,139, in a generic medical device with the characterizing features of claim 1. Particularly preferred production methods are set out in claims 2 and 3.
Die erfindungsgemäß vorgeschlagene, an sich bekannte Werkstoffklasse wird im folgenden "Silikonpolyurethan" genannt. Herstellung und Eigenschaften dieses Werkstoffes sind für die vorliegende Erfindung nicht kritisch und je nach den gewünschten Anforderungen ohne erfinderisches Zutun im Rahmen der beanspruchten Lehre aus dem Stand der Technik herleitbar.The material class known per se proposed according to the invention is hereinafter referred to as "silicone polyurethane". The production and properties of this material are not critical to the present invention and, depending on the desired requirements, can be derived from the prior art without inventive step within the framework of the claimed teaching.
Als Metallionen abgebende, mikrobizide, oligodynamisch wirksame Substanz werden z. B. Metallsalze, deren Oxide und Carbide sowie metallorganische Verbindungen verstanden, wie sie in der Medizin bezüglich Wirkung und Anwendung wohlbekannt sind.As a metal ion, microbicidal, oligodynamically active substance z. B. metal salts, their oxides and carbides as well as organometallic compounds understood as they are well known in medicine with regard to effect and application.
Die erfindungsgemäß 1- bis15prozentige räumliche Einbettung der aktiven Substanzen in die Silikonpolyurethan-Matrix erhöht die nutzbare Menge der zur Verfügung stehenden Ionen gegenüber den üblichen Beschichtungen um 40% und mehr.The spatial embedding of the active substances into the silicone-polyurethane matrix according to the invention by 1 to 15 percent increases the usable amount of the ions available compared to the usual coatings by 40% and more.
Überraschenderweise wurde gefunden, daß der Kontakt von Körperflüssigkeit mit den inneren Bereichen des bisher nur für andere Zwecke als vorteilhaft bekannten Silikonpolyurethan-Werkstoffes sicher gewährleistet ist, auch wenn die Polymermatrix für gattungsgemäße Geräte übliche Dicken von bis zu 2 mm aufweist.Surprisingly, it has been found that the contact of body fluid with the inner areas of the silicone polyurethane material, which has hitherto been known only for other purposes as advantageous, is reliably ensured, even if the polymer matrix for devices of the generic type has customary thicknesses of up to 2 mm.
Die Erfindung ist vorzugsweise, jedoch nicht ausschließlich, dann anzuwenden, wenn die betreffenden Geräte nicht nur vorübergehend, sondern länger im Körpergewebekontakt verbleiben müssen; sie umfaßt z. B. Endoprothesen, Katheter, Sonden, Endoskope, Implantate und Dränagen.The invention is preferably, but not exclusively, to be used when the devices in question must remain in contact with body tissue not only temporarily, but longer; it includes e.g. B. endoprostheses, catheters, probes, endoscopes, implants and drainage.
Da die das Gerät bildende polymere Matrix aus Silikonpolyurethan erfindungsgemäß zur Gänze den oligodynamischen Wirkstoff enthält, tritt, neben dem Vorteil der Abgabe der Metallionen zu beiden Außenflächen des Gerätekörpers hin, noch der vorteilhafte Effekt auf, daß zu Beginn der Anwendung, wo eine erhöhte Zahl von Bakterien, Mikroben und Keimen anwesend sein kann, eine erhöhte Menge an Wirkstoff mit abgegeben wird, sobald alle Oberflächenbereiche der Matrix mit Körperflüssigkeit durchtränkt sind. Nach längerer Verweildauer steht ein stetig sich verminderndes Angebot an Metallionen zur Verfügung, deren Abgabe nunmehr von ihrer Weglänge bei der Wanderung aus dem Inneren der Matrix an deren Oberfläche bestimmt wird.Since the polymer matrix made of silicone polyurethane which forms the device according to the invention contains the entire oligodynamic active ingredient, in addition to the advantage of releasing the metal ions to both outer surfaces of the device body, there is also the advantageous effect that at the beginning of the application, where an increased number of Bacteria, microbes and germs can be present, an increased amount of active ingredient is released as soon as all surface areas of the matrix are saturated with body fluid. After a longer period of time, there is a steadily decreasing supply of metal ions, the release of which is now determined by their path length during the migration from the interior of the matrix to its surface.
Zu diesem Zeitpunkt muß aber auch nur noch gewährleistet sein, daß die - geringe - Anzahl potentiell neu hinzukommender Keime sofort abgetötet wird. Die erfindungsgemäße Ausgestaltung des medizinischen Gerätes paßt somit die Abgaberate an Metallionen der Menge der momentan zu bekämpfenden Organismen von selbst an.At this point, however, it only has to be ensured that the - small - number of potentially new germs is immediately killed. The configuration of the medical device according to the invention thus automatically adjusts the rate of release of metal ions to the amount of organisms to be controlled.
Zweckmäßigerweise sollte die Metallionen abgebende Substanz in der Matrix keine Korngrößen größer als 50 µm enthalten, da ein Überschreiten dieser Grenze die mechanische Stabilität der Matrix negativ beeinflussen kann.The metal ion-releasing substance should expediently not contain any grain sizes larger than 50 μm, since exceeding this limit can have a negative effect on the mechanical stability of the matrix.
Bei erfindungsgemäß ausgestalteten Harnröhrenkathetern wurde außerdem der vorteilhafte Effekt beobachtet, daß Inkrustationen am Katheter, d.h. Überkrustungen mit Mineralien, in deutlich vermindertem Maße oder gar nicht auftraten.In the case of urethral catheters designed according to the invention, the advantageous effect was also observed that incrustations on the catheter, i.e. Crusting with minerals, to a significantly reduced extent or not at all.
Ein bevorzugtes Verfahren zur Herstellung des erfindungsgemäßen Gerätes besteht darin, daß man das Polypol, das organische Silikonpolymer sowie das Isocyanat sowie gegebenenfalls die Kettenverlängerer und/oder Vernetzersubstanzen miteinander reagieren läßt und danach in die gewünschte Form bringt.A preferred method for producing the device according to the invention is that the polypol, the organic silicone polymer and the isocyanate and, if appropriate, the chain extenders and / or crosslinking substances are allowed to react with one another and then brought into the desired shape.
Erfindungsgemäß wird dabei die Metallionen abgebende Substanz mit einem Anteil an der Gesamtpolymermasse von 1 bis 15 Gew.-% als Pulver mit einer Korngröße ≦ 50 µm vor der Zugabe des Isocyanats zugemischt und gemeinsam mit dem Polyol entwässert. Durch diese Verfahrensabfolge und die Feinkörnigkeit der wirksamen Substanz bei der Zugabe werden folgende Vorteile erzielt:According to the invention, the metal ion-donating substance with a proportion of the total polymer mass of 1 to 15% by weight is admixed as a powder with a grain size ≦ 50 μm before the addition of the isocyanate and dewatered together with the polyol. The following advantages are achieved by this sequence of processes and the fine granularity of the active substance when added:
Die getrennten Arbeitsgänge des Trocknens der Metallionen abgebenden Substanz sowie des Polyols und/oder des Polyolgemisches werden zu einem einzigen Verfahrensschritt zusammengefaßt. Die Feinkörnigkeit garantiert die Möglichkeit, die aktive Substanz über den gesamten Querschnitt der Polymermatrix besonders gleichmäßig einzubringen. Ein weiteres, besonders bevorzugtes Verfahren besteht darin, daß man anstelle des Pulvers eine gut wasserlösliche, Metallionen abgebende Substanz verwendet und diese als wäßrige Lösung mit einem Feststoff-Anteil wie bei der oben beschriebenen Pulver-Zugabe und an gleicher Stelle wie oben zumischt, anschließend entwässert und dann das Isocyanat zugibt.The separate operations of drying the metal ion-releasing substance and the polyol and / or the polyol mixture are combined into a single process step. The fine grain guarantees the possibility of introducing the active substance particularly evenly over the entire cross section of the polymer matrix. A further, particularly preferred method consists in using a readily water-soluble, metal ion-releasing substance instead of the powder and admixing it as an aqueous solution with a solids content as in the powder addition described above and at the same point as above, and then dewatered and then add the isocyanate.
Diese Verfahrensvariante bietet den Vorteil, die aktive Substanz in kleinstmöglicher Form, nämlich als diskrete Ionen und damit optimal gleichmäßig, in die Matrix einführen zu können.This variant of the method offers the advantage of being able to introduce the active substance into the matrix in the smallest possible form, namely as discrete ions and thus in an optimally uniform manner.
Das anschließende Entwässern führt zu keinen größeren Kristall-Agglomeraten, da die polymere Matrix nur die Entstehung kleiner Kristalle (≦ 50 µm) zuläßt. Zweckmäßig wird dabei als oligodynamisch aktive Substanz Silbernitrat eingesetzt.The subsequent dewatering does not lead to larger crystal agglomerates, since the polymer matrix only allows the formation of small crystals (≦ 50 µm). Silver nitrate is expediently used as the oligodynamically active substance.
Die erfindungsgemäßen Verfahren besitzen weiterhin folgende Vorteile:The methods according to the invention also have the following advantages:
Es wird eine einstufige Formgebung und bakterizide/mikrobizide Ausrüstung des medizinischen Gerätes erzielt. Jegliche Nachbehandlung entfällt, wodurch das Handhaben von Lösungsmitteln, das Quellen oder Anlösen des Substrates oder Probleme bezüglich der Haftung von Beschichtungen vollständig umgangen werden können.A one-step shaping and bactericidal / microbicidal treatment of the medical device is achieved. Any post-treatment is eliminated, which completely eliminates the handling of solvents, the swelling or dissolving of the substrate or problems with the adhesion of coatings.
Will man einen thermoplastischen Werkstoff erhalten, wird das fertig hergestellte, mit Wirkstoff ausgerüstete Polyurethan granuliert, getrocknet und anschließend entweder spritzgegossen oder extrudiert. Für die Herstellung von duroplastischen Geräten, z. B. Sonden, erfolgt die Formgebung sofort nach der Reaktion der Ausgangsstoffe durch Ausgießen in ein Formteil.If you want to obtain a thermoplastic material, the finished polyurethane with active ingredient is granulated, dried and then either injection molded or extruded. For the production of thermoset devices, e.g. B. probes, the shaping takes place immediately after the reaction of the starting materials by pouring into a molded part.
In jedem Falle kann das gewünschte medizinische Gerät in einem kontinuierlich verlaufenden Verfahrensschritt hergestellt werden.In any case, the desired medical device can be manufactured in a continuous process step.
Anhand des folgenden Beispieles wird in nicht einschränkender Weise ein Herstellungsverfahren für ein medizinisches Gerät aus einem thermoplastischen Werkstoff detailliert beschrieben:The following example describes a manufacturing method for a medical device made of a thermoplastic material in a non-restrictive manner:
100 Teile eines OH-terminierten, bifunktionellen Polyesters mit dem Molekulargewicht 2.000 g/mol (Basis: Adipinsäure, Neopentylglykol plus Hexandiol), wie er sich unter der Bezeichnung Desmophen 2028 der Bayer AG im Handel befindet, werden mit 20 Teilen eines linearen, entständige Hydroxylgruppen aufweisenden Polydimethylsiloxans (Molekulargewicht 2.000 g/mol) und 6 Teilen pulverisierten Silbernitrats (Korngröße ≦ 50 µm) gemischt und eine Stunde bei 120° C im Vakuum entwässert. Danach wird das entstandene Präpolymer mit 40 Teilen Diphenylmethan-4,4′-diisocyanat gemischt und nach dem Ausreagieren mit 9 Teilen Butandiol die Polymerkette verlängert.100 parts of an OH-terminated, bifunctional polyester with a molecular weight of 2,000 g / mol (based on adipic acid, neopentyl glycol plus hexanediol), as it is commercially available under the name Desmophen 2028 from Bayer AG, are mixed with 20 parts of a linear, hydroxyl group polydimethylsiloxane (molecular weight 2,000 g / mol) and 6 parts of powdered silver nitrate (grain size ≦ 50 microns) mixed and dehydrated at 120 ° C in a vacuum. Then the resulting prepolymer is mixed with 40 parts of diphenylmethane-4,4'-diisocyanate and after the reaction with 9 parts of butanediol, the polymer chain is extended.
Das fertige Produkt wird auf der Heizplatte aushärten gelassen, anschließend granuliert und zwei Stunden bei 110°C in einem Warmluftofen getrocknet. Zum Schluß wird das Granulat auf einer Spritzgießmaschine in die Form eines Harnröhrenkatheters gebracht.The finished product is allowed to harden on the hot plate, then granulated and dried in a warm air oven at 110 ° C. for two hours. Finally, the granules are shaped into an urethral catheter on an injection molding machine.
Der so gefertigte Katheter besizt die folgenden Materialeigenschaften:
Zugfestigkeit (DIN 53 504) : 20 MPa
Bruchdehnung (DIN 53 504) : 500%
Härte (DIN 53 305) : 70 shore A
Diese Materialdaten zeigen die mechanische Eignung des thermoplastischen Werkstoffes für die Herstellung von Kathetern und Implantaten.The catheter manufactured in this way has the following material properties:
Tensile strength (DIN 53 504): 20 MPa
Elongation at break (DIN 53 504): 500%
Hardness (DIN 53 305): 70 shore A
These material data show the mechanical suitability of the thermoplastic material for the production of catheters and implants.
Die folgende Tabelle zeigt in qualitativer und quantitativer Darstellung die mikrobizide Wirkung sowie die Abgabefähigkeit an oligodynamisch wirkenden Silberionen für eine Polyurethanmatrix gemäß dem Stand der Technik im Vergleich mit einer Silikonpolyurethan-Matrix gemäß der vorliegenden Erfindung:
Claims (3)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
AT88107039T ATE75953T1 (en) | 1987-08-04 | 1988-05-03 | MEDICAL DEVICE AND METHOD OF PRODUCTION. |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
DE3725728A DE3725728A1 (en) | 1987-08-04 | 1987-08-04 | MEDICAL DEVICE AND METHOD FOR THE PRODUCTION THEREOF |
DE3725728 | 1987-08-04 |
Publications (3)
Publication Number | Publication Date |
---|---|
EP0302186A2 true EP0302186A2 (en) | 1989-02-08 |
EP0302186A3 EP0302186A3 (en) | 1990-08-22 |
EP0302186B1 EP0302186B1 (en) | 1992-05-13 |
Family
ID=6332971
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP88107039A Expired - Lifetime EP0302186B1 (en) | 1987-08-04 | 1988-05-03 | Medical device and method for making it |
Country Status (11)
Country | Link |
---|---|
US (1) | US4973320A (en) |
EP (1) | EP0302186B1 (en) |
JP (1) | JPH01230368A (en) |
AT (1) | ATE75953T1 (en) |
DE (2) | DE3725728A1 (en) |
DK (1) | DK170231B1 (en) |
ES (1) | ES2031172T3 (en) |
FI (1) | FI91827C (en) |
GR (1) | GR3005190T3 (en) |
NO (1) | NO174573C (en) |
PT (1) | PT88189B (en) |
Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0399096A2 (en) * | 1989-05-22 | 1990-11-28 | Firma Carl Freudenberg | Tubular or annular elastic sleeves having microbicidal properties for urinary catheters |
EP0567627A1 (en) * | 1991-11-14 | 1993-11-03 | POLER, Stanley | Secondary eye growth impeding device and method |
EP0579995A1 (en) * | 1992-07-04 | 1994-01-26 | STERIMED Medizinprodukte GmbH | Catheterset |
WO1994027652A1 (en) * | 1993-05-20 | 1994-12-08 | Michael Hartmann | Endotracheal tube |
WO1998013405A1 (en) * | 1996-09-23 | 1998-04-02 | Cardiac Crc Nominees Pty. Ltd. | Polysiloxane-containing polyurethane elastomeric compositions |
WO2004017738A1 (en) * | 2002-08-26 | 2004-03-04 | C.R. Bard, Inc. | Antimicrobial compositions containing colloids of oligodynamic metals |
US6716895B1 (en) | 1999-12-15 | 2004-04-06 | C.R. Bard, Inc. | Polymer compositions containing colloids of silver salts |
Families Citing this family (61)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2586435B1 (en) * | 1985-08-26 | 1988-04-22 | Beugnet Sa | MOBILE PACKAGING RECONDITIONING MACHINE |
FI95816C (en) | 1989-05-04 | 1996-03-25 | Ad Tech Holdings Ltd | Antimicrobial article and method of making the same |
US5271736A (en) * | 1991-05-13 | 1993-12-21 | Applied Medical Research | Collagen disruptive morphology for implants |
US5827247A (en) * | 1991-08-20 | 1998-10-27 | Bioderm | External incontinence device and vapor-absorptive adhesive compositions |
DE4143239A1 (en) * | 1991-12-31 | 1993-07-01 | Joerg Dipl Chem Schierholz | PHARMACEUTICAL ACTIVE SUBSTANCES CONTAINING AN IMPLANTABLE DEVICE FROM A POLYMERIC MATERIAL AND METHOD FOR THE PRODUCTION THEREOF |
US5681575A (en) * | 1992-05-19 | 1997-10-28 | Westaim Technologies Inc. | Anti-microbial coating for medical devices |
GEP20002074B (en) * | 1992-05-19 | 2000-05-10 | Westaim Tech Inc Ca | Modified Material and Method for its Production |
DE4226810C1 (en) * | 1992-08-13 | 1994-01-27 | Theodor Dipl Ing Krall | Hoses and other objects made of plastic for medical use, which are not colonized by germs and processes for their manufacture |
US5409467A (en) * | 1992-10-02 | 1995-04-25 | Board Of Regents, The University Of Texas System | Antimicrobial catheter |
US5324275A (en) * | 1992-10-02 | 1994-06-28 | Board Of Regeants, University Of Texas System | Antimicrobial medical devices |
US6287484B1 (en) | 1992-11-12 | 2001-09-11 | Robert Hausslein | Iontophoretic material |
US5534288A (en) * | 1993-03-23 | 1996-07-09 | United States Surgical Corporation | Infection-resistant surgical devices and methods of making them |
US5848995A (en) * | 1993-04-09 | 1998-12-15 | Walder; Anthony J. | Anti-infective medical article and method for its preparation |
DE4403016A1 (en) * | 1994-02-01 | 1995-08-03 | Krall Theodor Dipl Ing | Microbicidal plastic articles partic. for medical use |
ES2190477T3 (en) * | 1995-11-17 | 2003-08-01 | Ursatec Verpackung Gmbh | FLUID DISPENSER DESIGNED TO PROTECT CONTENT FROM CONTAMINATION. |
DE19638570A1 (en) * | 1996-09-20 | 1998-03-26 | Bayer Ag | Active ingredient-containing thermoplastic polyurethanes |
US6013106A (en) * | 1997-01-22 | 2000-01-11 | St. Jude Medical, Inc. | Medical article with adhered antimicrobial metal ions and related methods |
US6001067A (en) | 1997-03-04 | 1999-12-14 | Shults; Mark C. | Device and method for determining analyte levels |
US8527026B2 (en) | 1997-03-04 | 2013-09-03 | Dexcom, Inc. | Device and method for determining analyte levels |
WO1999009997A1 (en) | 1997-08-26 | 1999-03-04 | Board Of Regents, The University Of Texas System | Edta and other chelators with or without antifungal antimicrobial agents for the prevention and treatment of fungal infections |
US6113636A (en) * | 1997-11-20 | 2000-09-05 | St. Jude Medical, Inc. | Medical article with adhered antimicrobial metal |
US6267782B1 (en) | 1997-11-20 | 2001-07-31 | St. Jude Medical, Inc. | Medical article with adhered antimicrobial metal |
DE19814133A1 (en) * | 1998-03-30 | 1999-10-07 | Espe Dental Ag | Self-disinfecting plastics and their use in the dental and dental technology field |
US6329488B1 (en) * | 1998-11-10 | 2001-12-11 | C. R. Bard, Inc. | Silane copolymer coatings |
US6596401B1 (en) | 1998-11-10 | 2003-07-22 | C. R. Bard Inc. | Silane copolymer compositions containing active agents |
US6168580B1 (en) * | 1999-03-26 | 2001-01-02 | Iontophoretics Corporation | Antimicrobial device and methods for long-term catheters |
US7179849B2 (en) | 1999-12-15 | 2007-02-20 | C. R. Bard, Inc. | Antimicrobial compositions containing colloids of oligodynamic metals |
US6579539B2 (en) | 1999-12-22 | 2003-06-17 | C. R. Bard, Inc. | Dual mode antimicrobial compositions |
US20040151755A1 (en) * | 2000-12-21 | 2004-08-05 | Osman Rathore | Antimicrobial lenses displaying extended efficacy, processes to prepare them and methods of their use |
EP1395268B1 (en) * | 2001-05-25 | 2005-01-19 | Gorm Danscher | A method of implanting heavy metal such as nobel metal, e.g. gold, and metal for use in implantation |
DE10134447B4 (en) * | 2001-07-16 | 2006-04-20 | Gkss-Forschungszentrum Geesthacht Gmbh | Carrier membrane for biohybrid organs, method of preparation and use |
US20030032874A1 (en) | 2001-07-27 | 2003-02-13 | Dexcom, Inc. | Sensor head for use with implantable devices |
CN1612804A (en) | 2001-12-03 | 2005-05-04 | C·R·巴德公司 | Microbe-resistant medical device, microbe-resistant polymeric coating and methods for producing same |
US7613491B2 (en) | 2002-05-22 | 2009-11-03 | Dexcom, Inc. | Silicone based membranes for use in implantable glucose sensors |
US8364229B2 (en) | 2003-07-25 | 2013-01-29 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
US7828728B2 (en) | 2003-07-25 | 2010-11-09 | Dexcom, Inc. | Analyte sensor |
US7226978B2 (en) | 2002-05-22 | 2007-06-05 | Dexcom, Inc. | Techniques to improve polyurethane membranes for implantable glucose sensors |
EP1648298A4 (en) | 2003-07-25 | 2010-01-13 | Dexcom Inc | Oxygen enhancing membrane systems for implantable devices |
US7761130B2 (en) | 2003-07-25 | 2010-07-20 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US9763609B2 (en) | 2003-07-25 | 2017-09-19 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
WO2005012873A2 (en) | 2003-07-25 | 2005-02-10 | Dexcom, Inc. | Electrode systems for electrochemical sensors |
US7591801B2 (en) | 2004-02-26 | 2009-09-22 | Dexcom, Inc. | Integrated delivery device for continuous glucose sensor |
DE10338261A1 (en) * | 2003-08-18 | 2005-03-10 | Hansgrohe Ag | Sanitary hose with antimicrobial equipment |
US8423114B2 (en) | 2006-10-04 | 2013-04-16 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
US11633133B2 (en) | 2003-12-05 | 2023-04-25 | Dexcom, Inc. | Dual electrode system for a continuous analyte sensor |
DE602004029092D1 (en) | 2003-12-05 | 2010-10-21 | Dexcom Inc | CALIBRATION METHODS FOR A CONTINUOUSLY WORKING ANALYTIC SENSOR |
US8808228B2 (en) | 2004-02-26 | 2014-08-19 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
US20050228216A1 (en) * | 2004-04-08 | 2005-10-13 | Vries Jan A D | Method for treating gastroesophageal reflux disease |
US8277713B2 (en) | 2004-05-03 | 2012-10-02 | Dexcom, Inc. | Implantable analyte sensor |
US8744546B2 (en) | 2005-05-05 | 2014-06-03 | Dexcom, Inc. | Cellulosic-based resistance domain for an analyte sensor |
US20200037874A1 (en) | 2007-05-18 | 2020-02-06 | Dexcom, Inc. | Analyte sensors having a signal-to-noise ratio substantially unaffected by non-constant noise |
US20080306444A1 (en) | 2007-06-08 | 2008-12-11 | Dexcom, Inc. | Integrated medicament delivery device for use with continuous analyte sensor |
EP4159114B1 (en) | 2007-10-09 | 2024-04-10 | DexCom, Inc. | Integrated insulin delivery system with continuous glucose sensor |
US8682408B2 (en) | 2008-03-28 | 2014-03-25 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
US8583204B2 (en) | 2008-03-28 | 2013-11-12 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
US11730407B2 (en) | 2008-03-28 | 2023-08-22 | Dexcom, Inc. | Polymer membranes for continuous analyte sensors |
EP3795987B1 (en) | 2008-09-19 | 2023-10-25 | Dexcom, Inc. | Particle-containing membrane and particulate electrode for analyte sensors |
WO2014209095A1 (en) | 2013-06-25 | 2014-12-31 | Servicios Administrates Penoles, S.A. De C.V. | Bacteriostatic and fungistatic additive in masterbatch for application in plastics, and method for producing same |
WO2017134049A1 (en) | 2016-02-01 | 2017-08-10 | Schierholz Jörg Michael | Implantable medical products, a process for the preparation thereof, and use thereof |
AU2018354120A1 (en) | 2017-10-24 | 2020-04-23 | Dexcom, Inc. | Pre-connected analyte sensors |
US11331022B2 (en) | 2017-10-24 | 2022-05-17 | Dexcom, Inc. | Pre-connected analyte sensors |
Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3562352A (en) * | 1968-09-06 | 1971-02-09 | Avco Corp | Polysiloxane-polyurethane block copolymers |
US4054139A (en) * | 1975-11-20 | 1977-10-18 | Crossley Kent B | Oligodynamic catheter |
EP0068385A1 (en) * | 1981-06-22 | 1983-01-05 | Kanegafuchi Kagaku Kogyo Kabushiki Kaisha | Thermoplastic elastomers for medical use as moulded articles brought into direct contact with blood |
US4581028A (en) * | 1984-04-30 | 1986-04-08 | The Trustees Of Columbia University In The City Of New York | Infection-resistant materials and method of making same through use of sulfonamides |
US4592920A (en) * | 1983-05-20 | 1986-06-03 | Baxter Travenol Laboratories, Inc. | Method for the production of an antimicrobial catheter |
EP0190504A2 (en) * | 1984-12-28 | 1986-08-13 | Johnson Matthey Public Limited Company | Antimicrobial compositions |
EP0206024A2 (en) * | 1985-06-07 | 1986-12-30 | Becton, Dickinson and Company | Antimicrobial surfaces and inhibition of microorganism growth thereby |
EP0207624A2 (en) * | 1985-05-30 | 1987-01-07 | The Trustees of Columbia University in the City of New York | Method for preparing infection-resistant materials |
Family Cites Families (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3279996A (en) * | 1962-08-28 | 1966-10-18 | Jr David M Long | Polysiloxane carrier for controlled release of drugs and other agents |
US4603152A (en) * | 1982-11-05 | 1986-07-29 | Baxter Travenol Laboratories, Inc. | Antimicrobial compositions |
JPS6121104A (en) * | 1984-07-10 | 1986-01-29 | Adeka Argus Chem Co Ltd | Photo-polymerization initiator |
US4867968A (en) * | 1987-12-29 | 1989-09-19 | Florida-Kansas Health Care, Inc. | Elastomeric composition containing therapeutic agents and articles manufactured therefrom |
-
1987
- 1987-08-04 DE DE3725728A patent/DE3725728A1/en active Granted
-
1988
- 1988-05-03 AT AT88107039T patent/ATE75953T1/en not_active IP Right Cessation
- 1988-05-03 EP EP88107039A patent/EP0302186B1/en not_active Expired - Lifetime
- 1988-05-03 DE DE8888107039T patent/DE3871016D1/en not_active Expired - Lifetime
- 1988-05-03 ES ES198888107039T patent/ES2031172T3/en not_active Expired - Lifetime
- 1988-05-31 NO NO882393A patent/NO174573C/en unknown
- 1988-06-07 DK DK309688A patent/DK170231B1/en not_active IP Right Cessation
- 1988-06-07 FI FI882682A patent/FI91827C/en not_active IP Right Cessation
- 1988-07-27 JP JP63187945A patent/JPH01230368A/en active Granted
- 1988-08-02 US US07/227,374 patent/US4973320A/en not_active Expired - Fee Related
- 1988-08-03 PT PT88189A patent/PT88189B/en not_active IP Right Cessation
-
1992
- 1992-07-16 GR GR910402111T patent/GR3005190T3/el unknown
Patent Citations (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3562352A (en) * | 1968-09-06 | 1971-02-09 | Avco Corp | Polysiloxane-polyurethane block copolymers |
US4054139A (en) * | 1975-11-20 | 1977-10-18 | Crossley Kent B | Oligodynamic catheter |
EP0068385A1 (en) * | 1981-06-22 | 1983-01-05 | Kanegafuchi Kagaku Kogyo Kabushiki Kaisha | Thermoplastic elastomers for medical use as moulded articles brought into direct contact with blood |
US4592920A (en) * | 1983-05-20 | 1986-06-03 | Baxter Travenol Laboratories, Inc. | Method for the production of an antimicrobial catheter |
US4581028A (en) * | 1984-04-30 | 1986-04-08 | The Trustees Of Columbia University In The City Of New York | Infection-resistant materials and method of making same through use of sulfonamides |
EP0190504A2 (en) * | 1984-12-28 | 1986-08-13 | Johnson Matthey Public Limited Company | Antimicrobial compositions |
EP0207624A2 (en) * | 1985-05-30 | 1987-01-07 | The Trustees of Columbia University in the City of New York | Method for preparing infection-resistant materials |
EP0206024A2 (en) * | 1985-06-07 | 1986-12-30 | Becton, Dickinson and Company | Antimicrobial surfaces and inhibition of microorganism growth thereby |
Cited By (12)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0399096A2 (en) * | 1989-05-22 | 1990-11-28 | Firma Carl Freudenberg | Tubular or annular elastic sleeves having microbicidal properties for urinary catheters |
EP0399096A3 (en) * | 1989-05-22 | 1991-03-06 | Firma Carl Freudenberg | Tubular or annular elastic sleeves having microbicidal properties for urinary catheters |
EP0567627A1 (en) * | 1991-11-14 | 1993-11-03 | POLER, Stanley | Secondary eye growth impeding device and method |
EP0567627A4 (en) * | 1991-11-14 | 1994-06-22 | Stanley Poler | Secondary eye growth impeding device and method |
EP0579995A1 (en) * | 1992-07-04 | 1994-01-26 | STERIMED Medizinprodukte GmbH | Catheterset |
WO1994027652A1 (en) * | 1993-05-20 | 1994-12-08 | Michael Hartmann | Endotracheal tube |
US5725510A (en) * | 1993-05-20 | 1998-03-10 | Hartmann; Michael | Endotracheal tube |
WO1998013405A1 (en) * | 1996-09-23 | 1998-04-02 | Cardiac Crc Nominees Pty. Ltd. | Polysiloxane-containing polyurethane elastomeric compositions |
US6313254B1 (en) | 1996-09-23 | 2001-11-06 | Cardiac Crc Nominees Pty Ltd | Polysiloxane-containing polyurethane elastomeric compositions |
US6627724B2 (en) | 1996-09-23 | 2003-09-30 | Aortech Biomaterials Pty Ltd | Polysiloxane-containing polyurethane elastomeric compositions |
US6716895B1 (en) | 1999-12-15 | 2004-04-06 | C.R. Bard, Inc. | Polymer compositions containing colloids of silver salts |
WO2004017738A1 (en) * | 2002-08-26 | 2004-03-04 | C.R. Bard, Inc. | Antimicrobial compositions containing colloids of oligodynamic metals |
Also Published As
Publication number | Publication date |
---|---|
FI91827C (en) | 1994-08-25 |
DE3871016D1 (en) | 1992-06-17 |
ATE75953T1 (en) | 1992-05-15 |
ES2031172T3 (en) | 1992-12-01 |
JPH0553142B2 (en) | 1993-08-09 |
DK170231B1 (en) | 1995-07-10 |
EP0302186A3 (en) | 1990-08-22 |
PT88189B (en) | 1993-09-30 |
PT88189A (en) | 1989-06-30 |
FI882682A0 (en) | 1988-06-07 |
GR3005190T3 (en) | 1993-05-24 |
NO882393D0 (en) | 1988-05-31 |
NO174573C (en) | 1994-06-01 |
FI91827B (en) | 1994-05-13 |
DE3725728A1 (en) | 1989-02-16 |
DK309688A (en) | 1989-02-05 |
NO882393L (en) | 1989-02-06 |
US4973320A (en) | 1990-11-27 |
JPH01230368A (en) | 1989-09-13 |
EP0302186B1 (en) | 1992-05-13 |
DE3725728C2 (en) | 1989-11-16 |
FI882682A (en) | 1989-02-05 |
NO174573B (en) | 1994-02-21 |
DK309688D0 (en) | 1988-06-07 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP0302186B1 (en) | Medical device and method for making it | |
EP1243259B1 (en) | Sustained release preparation comprising one or more antibiotics and polymers | |
DE602004004557T2 (en) | LUBRICANT COMPOSITIONS, THEIR PREPARATION AND ARTICLES COATED THEREFOR | |
EP0748634B1 (en) | Implant, its use in surgery and method for its manufacture | |
EP1536848B1 (en) | Methods for producing an anti-microbial plastic product | |
DE69629128T2 (en) | TRICLOSAN CONTAINING MEDICAL DEVICES | |
EP1796750B1 (en) | Antimicrobial implant with a flexible porous structure in the form of a sprayed non-woven | |
DE10043151A1 (en) | Bone cement with antimicrobial effectiveness | |
DE19936059A1 (en) | Production of antimicrobial plastic articles, especially catheters, involves pretreatment with colloidal metal, especially colloidal silver, before the final moulding process | |
EP1210386B1 (en) | Method of producing antimicrobial synthetic bodies with improved long-term behavior | |
WO2004034930A2 (en) | Bladder implant | |
WO2008019782A2 (en) | Dispersions of nanoureas containing active ingredients | |
EP2185208B1 (en) | Breast implant having antibacterial effect | |
DE10332680A1 (en) | Use of antiseptic agents in PMMA bone cements | |
DE60118602T2 (en) | LUBRICANT COATING WITH PHARMACOLOGICAL ACTIVE SUBSTANCES | |
DE102019219355B4 (en) | Implants, implant components and processes for their manufacture | |
EP1328306B1 (en) | Material for producing products having fibrinolytic and/or antibacterial properties | |
DE3134152A1 (en) | Carrier which contains antimicrobial agents and its use | |
EP1277484B1 (en) | Urological implant | |
DE10013248A1 (en) | Production of antimicrobial plastic articles, especially catheters, involves pretreatment with colloidal metal, especially colloidal silver, before the final moulding process | |
DE69133414T2 (en) | ELASTOMER POLYURETHANE OR POLYURETHANE-UREA-COMPOSITIONS | |
DE10331324A1 (en) | A process for preparation of an antimicrobial plastics product useful in medicine, e.g. for the production antimicrobial plastics urological catheters |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
PUAI | Public reference made under article 153(3) epc to a published international application that has entered the european phase |
Free format text: ORIGINAL CODE: 0009012 |
|
AK | Designated contracting states |
Kind code of ref document: A2 Designated state(s): AT BE CH DE ES FR GB GR IT LI LU NL SE |
|
PUAL | Search report despatched |
Free format text: ORIGINAL CODE: 0009013 |
|
AK | Designated contracting states |
Kind code of ref document: A3 Designated state(s): AT BE CH DE ES FR GB GR IT LI LU NL SE |
|
17P | Request for examination filed |
Effective date: 19900713 |
|
17Q | First examination report despatched |
Effective date: 19911022 |
|
GRAA | (expected) grant |
Free format text: ORIGINAL CODE: 0009210 |
|
ITF | It: translation for a ep patent filed |
Owner name: BARZANO' E ZANARDO ROMA S.P.A. |
|
AK | Designated contracting states |
Kind code of ref document: B1 Designated state(s): AT BE CH DE ES FR GB GR IT LI LU NL SE |
|
REF | Corresponds to: |
Ref document number: 75953 Country of ref document: AT Date of ref document: 19920515 Kind code of ref document: T |
|
REF | Corresponds to: |
Ref document number: 3871016 Country of ref document: DE Date of ref document: 19920617 |
|
GBT | Gb: translation of ep patent filed (gb section 77(6)(a)/1977) | ||
ET | Fr: translation filed | ||
REG | Reference to a national code |
Ref country code: ES Ref legal event code: FG2A Ref document number: 2031172 Country of ref document: ES Kind code of ref document: T3 |
|
REG | Reference to a national code |
Ref country code: GR Ref legal event code: FG4A Free format text: 3005190 |
|
PLBE | No opposition filed within time limit |
Free format text: ORIGINAL CODE: 0009261 |
|
STAA | Information on the status of an ep patent application or granted ep patent |
Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT |
|
26N | No opposition filed | ||
ITTA | It: last paid annual fee | ||
EPTA | Lu: last paid annual fee | ||
EAL | Se: european patent in force in sweden |
Ref document number: 88107039.5 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: SE Payment date: 19950420 Year of fee payment: 8 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: CH Payment date: 19950427 Year of fee payment: 8 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: LU Payment date: 19950501 Year of fee payment: 8 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: GR Payment date: 19950505 Year of fee payment: 8 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: AT Payment date: 19950510 Year of fee payment: 8 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: FR Payment date: 19950511 Year of fee payment: 8 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: ES Payment date: 19950517 Year of fee payment: 8 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: NL Payment date: 19950531 Year of fee payment: 8 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: BE Payment date: 19950602 Year of fee payment: 8 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: GB Payment date: 19960430 Year of fee payment: 9 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: LU Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 19960503 Ref country code: AT Effective date: 19960503 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: SE Effective date: 19960504 Ref country code: ES Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 19960504 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: LI Effective date: 19960531 Ref country code: CH Effective date: 19960531 Ref country code: BE Effective date: 19960531 |
|
BERE | Be: lapsed |
Owner name: FIRMA CARL FREUDENBERG Effective date: 19960531 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: GR Free format text: THE PATENT HAS BEEN ANNULLED BY A DECISION OF A NATIONAL AUTHORITY Effective date: 19961130 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: NL Effective date: 19961201 |
|
REG | Reference to a national code |
Ref country code: GR Ref legal event code: MM2A Free format text: 3005190 |
|
REG | Reference to a national code |
Ref country code: CH Ref legal event code: PL |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: FR Effective date: 19970131 |
|
EUG | Se: european patent has lapsed |
Ref document number: 88107039.5 |
|
NLV4 | Nl: lapsed or anulled due to non-payment of the annual fee |
Effective date: 19961201 |
|
REG | Reference to a national code |
Ref country code: FR Ref legal event code: ST |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: GB Effective date: 19970503 |
|
GBPC | Gb: european patent ceased through non-payment of renewal fee |
Effective date: 19970503 |
|
PGFP | Annual fee paid to national office [announced via postgrant information from national office to epo] |
Ref country code: DE Payment date: 19990422 Year of fee payment: 12 |
|
REG | Reference to a national code |
Ref country code: ES Ref legal event code: FD2A Effective date: 19990503 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: DE Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES Effective date: 20010301 |
|
PG25 | Lapsed in a contracting state [announced via postgrant information from national office to epo] |
Ref country code: IT Free format text: LAPSE BECAUSE OF NON-PAYMENT OF DUE FEES;WARNING: LAPSES OF ITALIAN PATENTS WITH EFFECTIVE DATE BEFORE 2007 MAY HAVE OCCURRED AT ANY TIME BEFORE 2007. THE CORRECT EFFECTIVE DATE MAY BE DIFFERENT FROM THE ONE RECORDED. Effective date: 20050503 |